US8449500B2 - Flow pulsatility dampening devices for closed-loop controlled infusion systems - Google Patents

Flow pulsatility dampening devices for closed-loop controlled infusion systems Download PDF

Info

Publication number
US8449500B2
US8449500B2 US11941840 US94184007A US8449500B2 US 8449500 B2 US8449500 B2 US 8449500B2 US 11941840 US11941840 US 11941840 US 94184007 A US94184007 A US 94184007A US 8449500 B2 US8449500 B2 US 8449500B2
Authority
US
Grant status
Grant
Patent type
Prior art keywords
fluid
flow
infusion
dampening
pump
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active, expires
Application number
US11941840
Other versions
US20090131859A1 (en )
Inventor
Jorge Delcastillo
Alp Akonur
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Baxter Healthcare SA
Baxter International Inc
Original Assignee
Baxter Healthcare SA
Baxter International Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Grant date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142Pressure infusion, e.g. using pumps
    • A61M5/14212Pumping with an aspiration and an expulsion action
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16831Monitoring, detecting, signalling or eliminating infusion flow anomalies
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04POSITIVE DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04BPOSITIVE DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B39/00Component parts, details, or accessories, of pumps or pumping systems, not otherwise provided for in, or of interest apart from, groups F04B25/00 - F04B37/00
    • F04B39/0027Pulsation and noise damping means
    • F04B39/005Pulsation and noise damping means with direct action on the fluid flow using absorptive materials
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2206/00Characteristics of a physical parameter; associated device therefor
    • A61M2206/10Flow characteristics
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2206/00Characteristics of a physical parameter; associated device therefor
    • A61M2206/10Flow characteristics
    • A61M2206/22Flow characteristics eliminating pulsatile flows, e.g. by the provision of a dampening chamber
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142Pressure infusion, e.g. using pumps
    • A61M5/14212Pumping with an aspiration and an expulsion action
    • A61M5/14216Reciprocating piston type
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142Pressure infusion, e.g. using pumps
    • A61M5/14212Pumping with an aspiration and an expulsion action
    • A61M5/14224Diaphragm type
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142Pressure infusion, e.g. using pumps
    • A61M5/14212Pumping with an aspiration and an expulsion action
    • A61M5/14228Pumping with an aspiration and an expulsion action with linear peristaltic action, i.e. comprising at least three pressurising members or a helical member
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142Pressure infusion, e.g. using pumps
    • A61M5/14212Pumping with an aspiration and an expulsion action
    • A61M5/14232Roller pumps
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/172Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body electrical or electronic

Abstract

A flow monitoring infusion system that includes an infusion circuit having a fluid with a pulsatile fluid flow flowing therethrough. The infusion circuit includes a dampening element having a dampening chamber that absorbs the pressure fluctuations of the pulsatile fluid flow to transform the pulsatile fluid flow to a more smooth fluid flow. A fluid flow sensor that measures the flowrate of the more smooth fluid flow is disposed along the infusion circuit downstream of the dampening element.

Description

BACKGROUND

The present disclosure generally relates to medical fluid delivery systems. In particular, the present disclosure relates to devices and methods for transforming a generally pulsatile fluid flow in an infusion system to a smoother or less pulsatile fluid flow.

Liquid medicaments and other complex medical and therapeutic fluids are often administered to patients through infusion therapy. Typically, infusion therapy is accomplished by employing an infusion pump to force fluid through an infusion circuit and into a patient. In certain situations, such as when the infusion of fluid takes place over a long period of time with a patient that is ambulatory, it is desirable to use a disposable infusion system.

Because disposable infusion systems are disposable, such systems typically include relatively simple and inexpensive components. However, one of the difficulties encountered with using relatively simple and inexpensive components is that the components are often not compatible for use with one another. For example, the majority of simple and inexpensive infusion pumps generate a pulsatile or non-continuous fluid flow. Even durable and expensive pumps generate pulsatility. This pulsatile fluid flow is dynamic and has flowrate and pressure fluctuations that change very quickly. Further, most simple and inexpensive fluid flow sensors do not have the temporal resolution or the ability to sense and calculate the flowrate of a pulsatile fluid flow. The incompatibility of these components creates an obstacle to producing economical disposable infusion systems that have the ability to monitor the fluid flowrate within the infusion circuit.

In many infusion therapy applications a fluid is required to be administered to the patient at a certain fluid flowrate to be therapeutically effective. For example, in some applications, if the fluid is infused too slowly, the intended therapeutic effect may be diminished or totally non-existent. In other applications, infusion of a fluid into the body at too high a rate can create a dangerous or overdose situation. Thus, in a number of infusion therapy applications it is important for the user to be able to quickly and accurately determine the rate of fluid flow through the system, so that the flowrate can be monitored and adjusted as needed.

In those instances in which it is important for the user to be able to determine flowrate, a disposable infusion set will often include either an infusion pump that generates a smooth fluid flow or a flow sensor that has the ability to monitor and calculate the flowrate of a pulsatile or non-continuous fluid flow. One of the disadvantages of using a smooth flow generating infusion pump or a flow sensor that can monitor pulsatile flow is that both of those components are relatively expensive and add appreciably to the overall cost of the disposable infusion set. In addition to increased cost, system components that are capable of achieving high resolution measurements often require complex circuitry, hardware and software architecture.

SUMMARY

The present disclosure provides an infusion system that includes a dampening element, which transforms a generally non-continuous or pulsatile flow of fluid within the infusion system into a generally smoother or less pulsatile fluid flow. The incorporation of a dampening element in to an infusion system provides a variety of benefits. For example, the transformation of a generally pulsatile fluid flow into a smoother fluid flow allows a relatively inexpensive fluid flow sensor, which does not have the temporal resolution to sense and calculate flowrate of a pulsatile flow of fluid, to be used to monitor and adjust such fluid flow. The ability to employ a relatively inexpensive flow sensor decreases the overall cost of the infusion system appreciably.

In general, the dampening element is disposed at a location along the fluid pathway of an infusion system and receives a fluid having a pulsatile fluid flow from a fluid source upstream of the dampening element. The dampening element includes a dampening chamber having a compressible gas, such as air, located therein. When the pulsatile fluid flow enters the dampening element, the gas within the chamber compresses to absorb the pressure fluctuations of the pulsatile fluid flow, thereby transforming the pulsatile fluid flow into a smoother or less pulsatile fluid flow. The smoother flow of fluid exits the dampening element and flows downstream through the remaining portion of the infusion system.

One aspect of the present disclosure relates generally to a flow monitoring infusing system that includes a fluid pathway containing a fluid that has a generally pulsatile fluid flow. The infusion system also includes a dampening chamber disposed along the fluid pathway. The dampening chamber contains a compressible gas that absorbs the pressure fluctuations of the pulsatile fluid flow to transform the pulsatile fluid flow to smoother fluid flow. The infusion system further includes a fluid flow sensor disposed along the infusion circuit downstream of the dampening element. The flow sensor measures the flowrate of the smooth fluid flow. In an embodiment, the flow sensor is a relatively inexpensive flow sensor that is intended to measure a generally smooth flow of fluid.

Another aspect of the present disclosure generally relates to infusion systems that transform a generally pulsatile fluid flow to a more smooth fluid flow. The infusion system includes an infusion pathway and an infusion pump that generates a generally pulsatile flow of fluid through the pathway. The infusion system also includes a generally tubular element defining a dampening chamber that is in fluid communication with the pathway. The dampening chamber contains a compressible gas that absorbs the pressure fluctuations of pulsatile fluid flow. The system also includes a flow sensor that monitors the flow of the smoothened fluid.

A further aspect of the present disclosure relates to a method for controlling the rate of fluid flow through an infusion system. The method includes flowing a pulsatile fluid flow through the infusion system. The pulsatile fluid flow is transformed into a smoothed fluid flow which is measured to determine the actual fluid flowrate. The actual fluid flowrate is compared to a desired fluid flowrate and the flow of pulsatile fluid is adjusted until the actual fluid flowrate is equal to the desired fluid flowrate.

Additional features and advantages are described herein, and will be apparent from, the following Detailed Description and the figures.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1 is a side view of one embodiment of an infusion system according to the present disclosure;

FIG. 2 is a perspective view of the dampening element shown in FIG. 1;

FIG. 3 is a side view of another embodiment of an infusion system according to the present disclosure;

FIG. 4 is an elevation view of another embodiment of a dampening member of the present disclosure; and

FIG. 5 is a schematic illustration of one embodiment of a closed-loop control system of the present disclosure.

DETAILED DESCRIPTION

Referring now to the drawings and in particular to FIG. 1, an infusion therapy system or set 10 for infusing fluids, such as medicaments or other therapeutic fluids, into a patient is provided. The infusion therapy system 10 in an embodiment is a disposable infusion system that includes relatively inexpensive component parts. In the embodiment shown, the infusion therapy system 10 includes a fluid supply 12, an infusion pump 14 and a fluid pathway 16. In general, the infusion pump 14 pumps fluid 18 from the fluid supply 12, through the infusion pathway 16, to an infusion device (not shown) that delivers the fluid to a patient. The infusion device can be any number of infusion devices, such as a catheter, implantable port, intravenous delivery device, shunt or other mechanism that interfaces with the patient to deliver fluid.

The infusion pump 14 is a pump that generates a pulsatile fluid flow having pressure fluctuations, such as a micro-diaphragm or a peristaltic pump. For example, the pump can for example be a micro-diaphragm pump provided by thinXXS Microtechnology AG, Zweib{grave over (r)}ücken, Germany. The pump itself can be disposable. Alternatively, the fluid carrying components of the pump are disposable. These types of pumps are often small in size, generally lightweight and relatively inexpensive. The pump 14 includes an inlet port 20 for receiving fluid and an outlet port 22 for expelling fluid. The inlet port 20 of the infusion pump 14 is connected to the distal end portion 24 of a fluid supply conduit 26, and the proximal end portion 28 of the fluid supply conduit 26 is connected to fluid supply 12. The connection between the fluid supply conduit 26 and the pump 14, and other connections of components described herein, can be any suitable type of permanent or removable connection known to those skilled in the art, such as a male-female luer type connection or an integral connection.

The fluid supply 12 may include a flexible dispensing bag 30 containing a fluid 18 to be infused into the patient. The dispensing bag 30 in an embodiment is made from a polymeric material and includes outlet port 32 that is connected to the proximal end portion 28 of fluid supply conduit 26. The dispensing bag 30 supplies the fluid 18 through the fluid supply conduit 26 to the infusion pump 14.

Infusion pathway 16 provides a fluid path from the pump 14 to an infusion device (not shown). Infusion pathway 16 can include a first fluid conduit 34 that has a proximal end portion 36 and a distal end portion 38. Proximal end portion 36 of first fluid conduit 34 is connected to outlet port 22 of infusion pump 14 and receives a pulsatile flow of fluid from the infusion pump. For example, the rollers of a race of a peristaltic pump create a generally pulsatile flow. The back and forth motion of a membrane or diaphragm in a membrane pump also creates non-continuous or pulsatile flow.

A pulsatility dampening device or element 40 is disposed along infusion pathway 16 at a location that is downstream of the infusion pump 14. Distal end portion 38 of first fluid conduit 34 is connected to dampening element 40. Dampening element 40 receives the pulsatile fluid flow and transforms it into a smoother or more continuous fluid flow.

Dampening element 40 shown in FIGS. 1 and 2 has a generally cylindrical body 42 defining a dampening chamber 44. Alternatively, element 40 has a rectangular or other suitable shape. In one embodiment, the dampening chamber has a volume between about eight milliliters (“ml”) and thirty ml. The dampening element body 42 includes a top wall 46, a bottom wall 48 and a generally cylindrical sidewall 50. Dampening element 40 can be made of a suitable polymeric material, such as a polymer material that does not react with the fluid being infused. Dampening element 40 includes an inlet port 52 and an outlet port 54 extending through sidewall 50 of the dampening element. Inlet port 52 and outlet port 54 are in fluid communication with dampening chamber 44.

In an embodiment, inlet port 52 and outlet port 54 are generally aligned so that the fluid flow path through dampening element 40 is substantially straight or linear. In the illustrated embodiment, inlet port 52 includes a central axis X and outlet port 54 includes a central axis Y. Inlet port 52 and outlet port 54 are disposed along the sidewall 50 so that axis X and axis Y are generally coaxial. Alternatively, inlet port 52 and outlet port 54 could be disposed along the sidewall 50 so that the inlet port and the outlet port are not aligned. For example, the outlet port 54 could be disposed along the sidewall 50 so its central axis Y, is not coaxial with axis X of the inlet port 52, or the inlet port and outlet port can be positioned so that the axis X and axis Y lay in different planes.

Inlet port 52 of dampening element 40 is connected to distal end portion 38 of first fluid conduit 34 so that dampening chamber 44 is in fluid communication with fluid path 16. As fluid 18 is infused into the system, fluid resistance and backpressure on the downstream side of dampening element 40 causes an increase of fluid pressure within the system. This increase in fluid pressure causes fluid 18 to partially fill the dampening chamber 44 so that the fluid level is above or covers inlet port 52 and outlet port 54.

As fluid 18 fills dampening chamber 44, the fluid traps and compresses gasses contained in space 56 above the fluid. The gas can be air or an otherwise compressible gas. As explained above, the pump provides a pulsatile or non-continuous fluid flow, which periodically increases and decreases in pressure at a regular interval as the fluid flows through the infusion system. This pulsatile fluid flow enters dampening chamber 44, and as the pressure of fluid 18 periodically increases, the gas within chamber 44 compresses to absorb the increases in pressure. This produces a smoother or more continuous flow of fluid that flows out of outlet port 54. In other words, the gas within space 56 provides a dampening quality wherein the pressure fluctuations of the pulsatile flow are absorbed by the gas to produce a less pulsatile or smoother flow of fluid out of the outlet port 54.

The dampening quality of the chamber and the smoothness of the fluid provided by dampening element 40 can depend on a variety of variables, such as the volume of the dampening chamber, the viscosity of the infusion fluid, the compressibility of the gas located within the dampening chamber and the backpressure within the fluid system. By adjusting these variables the dampening chamber can be optimized for a particular infusion application. Practically, the volume of the chamber is the mainly adjustable parameter. The viscosity of the fluid is set by the liquid to be infused. The backpressure in the system depends on the viscosity and geometrical properties of other disposable components within the circuit.

A proximal end portion 58 of a second fluid conduit 60 is connected to outlet 54 of dampening element 40 so that second fluid conduit 60 receives a generally smooth or continuous flow of fluid from the dampening element. A distal end portion 62 of second fluid conduit 60 is connected to an inlet port 64 of a flow monitor or flow sensor 66 that is disposed along the infusion circuit at a location downstream of dampening element 40. As the fluid flows through flow sensor 66 towards an outlet port 68 of the flow sensor, the flow sensor detects the rate of fluid flow. Because the dampening member has transformed the fluid flow to a smoother flow, a flow sensor for measuring pulsatile fluid flow is not needed, and flow sensor 66 can be of the type that is generally employed to monitor and calculate the flowrate of a generally smooth or slightly pulsatile flow. For example, the flow sensor can be an optical, laser or heat pulse, time-of-flight type non-invasive flowrate sensor. While non-invasive sensors are advantageous for sterility purposes, they are not critical for the present disclosure. Invasive flow sensors, such as positive displacement flow sensors, can be used alternatively.

In an embodiment, flow sensors that are generally only used to sense smooth fluid flow can be employed because they are relatively inexpensive when compared to flow sensors that have the ability to sense and monitor the flowrate of a fluid having a pulsatile flow. Further, it should be understood that these relatively inexpensive smooth fluid flow sensors are normally incompatible for use with the pulsatile fluid flow generating pumps described above.

After the fluid flows out of flow sensor 66, the fluid enters into a third fluid conduit 74 having a proximal end portion 76 connected to flow sensor outlet 68. The fluid flows through third fluid conduit 74 and into an infusion device (not shown, e.g., catheter or cannula) that is connected to distal end portion 78 of the third fluid conduit 74. The infusion device delivers the fluid to the patient.

In one embodiment, flow sensor 66 is connected to a processing unit 70 that receives a signal from the flow sensor and calculates the flowrate. The processing unit 70 can include a display device 72, such as a liquid crystal display, for indicating the flowrate to the user. Upon receiving flowrate information, the user may then use this information to adjust the pump as necessary so as to optimize and achieve the desired flowrate.

Optionally, processing unit 70 communicates with and controls infusion pump 14 with a closed-loop control, which adjusts the infusion pump actuator based on sensed flowrate information to optimize the flowrate. FIG. 5 illustrates one embodiment of a closed-loop control system 80 that can be employed to optimize the flowrate of fluid in the infusion system. Closed-loop control system 80 includes an input 82 to a summing junction 83. The user sets input 82 at a control unit, such as control unit 130 shown in FIG. 3. The input represents a desired flowrate for a particular infusion therapy application. Input 82 operates or is fed to a pump speed controller 84. Pump speed controller 84 is operably connected to and controls the pumping speed or pump settings of infusion pump 14.

In one embodiment, the pump speed of pump 14 is controlled by the amount of voltage or current that pump speed controller 84 supplies to pump 14. Input 82 tells pump speed controller 84 what initial voltage or current to use. Pump speed controller 84 supplies this initial amount of voltage or current to pump 14. The increase in voltage or current increases the pumping speed of pump 14, which in turn increases flowrate. Likewise, when input 82 receives a directive to decrease pump speed, pump speed controller 84 decreases the amount of voltage or current supplied to pump 14, which decreases the pumping speed and the flowrate.

As explained above, pump 14 provides a pulsatile or non-continuous flow of fluid to dampening element 40. Dampening element 40 converts the fluid flow into a smoother flow and the fluid flows to flow sensor 66. Flow sensor 66 senses the actual flowrate and sends a flowrate signal to processor 70. Processor 70 compares actual flowrate from sensor 66 to the inputted flowrate set at 82. If actual flowrate equals set flowrate, processor 70 does not modify input signal 82 at summer 83. If processor 70 determines the flowrate needs to be adjusted processor 70 communicates the needed adjustment to summer 83, which modifies input 82 to produce a modified signal to controller 84, which adjusts voltage or currents to pump 14 accordingly. Processor 70 can use only one or more or all of a proportional, integral and differential (“PID”) gain to modify input 82 at summer 83. PID control is known in the art. Closed-loop control 80 continuously monitors and adjusts the pump speed setting to have the sensed flowrate to the desired flowrate.

It is worth noting that a flowrate signal of a smooth flowing fluid sensed at sensor 66 is used to control an input to a generally pulsatile or non-continuous pump. Any one or more of the PID gains can be set empirically to optimize the feedback to account for the pulsatile/non-pulsatile mismatch. The resulting system is an inexpensive but accurate system.

FIG. 3 illustrates another embodiment of an infusion system 110, which is generally similar to infusion system 10 illustrated in FIG. 1. The infusion system 110 includes infusion pump 14, infusion pathway 16 and flow sensor 66. In this embodiment, the damping element 112 includes a generally tubular shaped dampening chamber 114 having a distal end 116 and a closed proximal end 118. The distal end portion 116 is in fluid communication with the fluid pathway. Dampening chamber 114 also extends in a generally perpendicular direction to the flow of fluid through the fluid passageway. The tubular dampening chamber 114 may be made of a polymeric flexible material. For example, the dampening chamber can be a length of a flexible tubing line. In one embodiment, the tubular dampening chamber 114 has a diameter of about 0.125 inches (3.2 mm) to about 0.25 inches (6.4 mm), a length of about 2 inches (5.1 cm) to about 10 inches (25.4 cm) and a volume of about 1 ml to about 3 ml.

In the illustrated embodiment, dampening element 112 includes a T-shaped three way connector 120 having a first port 122 in communication with distal end portion 38 of first fluid conduit 34, a second port 124 in communication with proximal end portion 58 of second fluid conduit 60 and a third port 126 in communication with tubular shaped dampening chamber 114. As fluid is infused, the resistance and backpressure down stream of the dampening element 112 causes fluid 18 to partially fill a portion of the tubular dampening chamber 114. As fluid fills dampening chamber 114, the fluid traps and compresses gas in space 128 above the fluid. Similar to the previous embodiment, as fluid pressure increases during the natural fluctuation of the pulsatile fluid flow, the increased pressure of the fluid is exerted against the gas in space 128. The gas compresses to absorb the increased fluid pressure and to convert the pulsatile fluid flow to a smoother or more continuous flow. The smoother flow of fluid exits out of outlet port 124 and flows through second fluid conduit 60 to flow sensor 66. Flow sensor 60 measures the fluid rate of the smooth fluid flow in a similar fashion as described above.

In an alternative embodiment, the first fluid conduit 34, second fluid conduit 60 and dampening chamber 114 could be connected to different ports of the T-shaped connector. For example, the dampening chamber 114 can be connected to the first port 122 of the T-shaped connector and the first fluid conduit 34 can be connected to the third port 126, or the dampening chamber 114 can be connected to the second port 124 and the second fluid conduit 60 can be connected to the third fluid port 126. While the dampening chamber can be connected to different ports, the dampening chamber should be either vertical to the fluid path or above the fluid path so that gas within the fluid chamber does not enter fluid being infused.

FIG. 4 illustrates another embodiment of a dampening element 132 that can by used in an infusion system to transform a pulsatile fluid flow to a generally smooth fluid flow. The dampening element 132 has a generally cylindrical body 134 defining a damping chamber 136. The body has a top wall 138, a bottom wall 140 and a circumferential sidewall 142. The dampening element 132 includes an inlet port 144 located through the sidewall 142 and an outlet port 146 located through the bottom wall 140. The inlet port 144 is connected to and receives a pulsatile flow of fluid from the first fluid conduit 34 into the dampening chamber 136. During the infusion therapy operation, the dampening chamber 136 is partially filled with fluid 18. Similar to the previous embodiments, the dampening chamber 136 has a space 148 that is occupied by a compressible gas that absorbs the pressure fluctuations of the pulsatile fluid flow.

The pulsatile fluid flow enters inlet port 144 from first fluid conduit 34. In the dampening chamber 136, the gas located within the space 148 absorbs the pressure fluctuations of the pulsatile fluid flow, transforming the fluid flow into a less pulsatile or smoother fluid flow. The smoother flow of fluid exits the dampening chamber 136 through the outlet 148 and flows into the second fluid conduit 60.

In the embodiments illustrated herein for dampening elements 40, 112 and 132, the dampening elements should be oriented as shown, such that the liquid/air interface is located above the respective outlet of the dampening chamber. For example, outlet 54 is located elevationally below the liquid/air interface of dampening element 40 in FIGS. 1 and 2. Outlet port 124 is located elevationally below the liquid/air interface of dampening element 112 in FIGS. 1 and 2. Outlet port 146 is located elevationally below the liquid/air interface of dampening element 132 in FIG. 4. In an alternative embodiment, any of dampening elements 40, 112 and 132 can have a flexible membrane or diaphragm that separates the liquid from the gas, the liquid side of the element being fully primed to the flexible membrane or diaphragm. The membrane and the compressibility of the gas here dampens the pulsatility of the fluid being pumped. The membrane also allows the dampening elements 40, 112 and 132 to be mounted in different orientations, which would allow an infusion pump incorporating any of the dampening elements to also be mounted in different orientations.

Infusion system 110 using any of the dampening elements discussed herein includes a control unit 130, which is in communication with the flow sensor 66 and the infusion pump 14. Using the control system of FIG. 5, the control unit 130 can be employed to create a closed-loop controlled infusion system that optimizes the flowrate of fluid through the infusion system. For example, a user enters a desired flowrate into the control unit 130. The control unit 130 communicates with the infusion pump 114 to set the pump to pump fluid at the desired flowrate. The control unit 130 receives information from the flow sensor 66 regarding the actual flowrate through the infusion circuit, and then processes the information to calculate the actual flowrate. The control unit 130 can include a PID control discussed above that compares the actual flowrate to the desired flowrate and adjusts infusion pump 14 as needed until the actual flowrate is equal to the desired flowrate.

It should be understood that various changes and modifications to the presently preferred embodiments described herein will be apparent to those skilled in the art. Such changes and modifications can be made without departing from the spirit and scope of the present subject matter and without diminishing its intended advantages. It is therefore intended that such changes and modifications be covered by the appended claims.

Claims (17)

The invention is claimed as follows:
1. A flow monitoring infusing system, comprising:
a liquid pathway for containing a liquid pumped at a non-continuous fluid flow;
a dampening chamber in communication with the liquid pathway, the dampening chamber configured to hold a compressed gas that absorbs pressure fluctuations of the non-continuous fluid flow to smoothen the non-continuous fluid flow, wherein the compressed gas is in direct fluid communication with the pumped liquid; and
a fluid flow sensor disposed along the liquid pathway downstream of the dampening chamber to measure the flowrate of the smoothened fluid flow.
2. The infusion system of claim 1, which includes a pulsatile infusion pump in communication with the fluid pathway for providing a non-continuous fluid flow.
3. The infusion system of claim 2, wherein the pulsatile infusion pump is selected from the group consisting of a membrane pump and a peristaltic pump.
4. The infusion system of claim 1, wherein the dampening chamber includes a generally cylindrical or rectangular body shape.
5. The infusion system of claim 1, wherein the dampening chamber is a length of tubing extending from the fluid pathway.
6. The infusion system of claim 1, wherein the dampening chamber has a volume between about 8 ml and about 30 ml.
7. The infusion system of claim 1, wherein the gas includes air.
8. The infusion system of claim 1, further including a closed-looped control system configured to optimize the flowrate.
9. The infusion system of claim 6, wherein the closed-looped control system includes a PID controller.
10. An infusion system comprising:
a fluid pathway;
an infusion pump for pumping a non-continuous flow of fluid through the fluid pathway;
a generally tubular shaped member defining a chamber that is in communication with the fluid pathway, the chamber containing a compressed gas that absorbs pressure fluctuations of the non-continuous fluid to smoothen the non-continuous flow, wherein the compressed gas is in direct fluid communication with the non-continuous flow of fluid;
a fluid flow sensor disposed along the fluid pathway downstream of the tubular shaped member, the flow sensor configured to measure a flowrate of the smoothened fluid flow, the fluid pathway extending from the pump, through the fluid sensor and downstream from an outlet of the fluid sensor; and
a control member operable with the flow sensor and the infusion pump, the control member configured to receive flowrate information from the flow sensor and to adjust the infusion pump based on the flowrate information.
11. The infusion system of claim 10, wherein the generally tubular shaped member is operably connected to the fluid pathway by a T-shaped connector.
12. The infusion system of claim 10, wherein the generally tubular shaped element comprises a length of flexible tubing.
13. The infusion system of claim 10, wherein the tubular shaped member extends in a generally perpendicular direction from the fluid pathway.
14. The infusion system of claim 10, wherein the chamber has a volume between about 8 ml and about 30 ml.
15. The infusion system of claim 10, wherein the control member includes a PID controller.
16. The infusion system of claim 10, wherein the infusion pump is selected from the group consisting of a membrane pump and a peristaltic pump.
17. A flow monitoring infusing system, comprising:
a fluid pathway for containing a fluid pumped at a non-continuous fluid flow;
a dampening chamber in communication with the fluid pathway, the dampening chamber configured to hold a gas that absorbs pressure fluctuations of the non-continuous fluid flow to smoothen the non-continuous fluid flow, wherein the compressed gas is in direct fluid communication with the pumped fluid; and
a fluid flow sensor disposed along the fluid pathway downstream of the dampening chamber to measure the flowrate of the smoothened fluid flow that flows through the fluid flow sensor.
US11941840 2007-11-16 2007-11-16 Flow pulsatility dampening devices for closed-loop controlled infusion systems Active 2028-06-17 US8449500B2 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US11941840 US8449500B2 (en) 2007-11-16 2007-11-16 Flow pulsatility dampening devices for closed-loop controlled infusion systems

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US11941840 US8449500B2 (en) 2007-11-16 2007-11-16 Flow pulsatility dampening devices for closed-loop controlled infusion systems
PCT/US2009/030299 WO2009065153A8 (en) 2007-11-16 2009-01-07 Flow pulsatility dampening devices for closed-loop controlled infusion systems
EP20090700037 EP2496284A2 (en) 2007-11-16 2009-01-07 Flow pulsatility dampening devices for closed-loop controlled infusion systems

Publications (2)

Publication Number Publication Date
US20090131859A1 true US20090131859A1 (en) 2009-05-21
US8449500B2 true US8449500B2 (en) 2013-05-28

Family

ID=40635483

Family Applications (1)

Application Number Title Priority Date Filing Date
US11941840 Active 2028-06-17 US8449500B2 (en) 2007-11-16 2007-11-16 Flow pulsatility dampening devices for closed-loop controlled infusion systems

Country Status (3)

Country Link
US (1) US8449500B2 (en)
EP (1) EP2496284A2 (en)
WO (1) WO2009065153A8 (en)

Families Citing this family (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8034020B2 (en) * 2008-06-19 2011-10-11 Carefusion 303, Inc. Optical flow sensor
US8366667B2 (en) * 2010-02-11 2013-02-05 Baxter International Inc. Flow pulsatility dampening devices
WO2012135555A3 (en) * 2011-03-29 2012-11-29 Prad Research And Development Limited System and method for reducing pressure fluctuations in an oilfield pumping system
CN102996395B (en) * 2011-09-13 2016-12-21 精工爱普生株式会社 Sending pump, a liquid circulation means, medical and electronic devices
JP6115014B2 (en) * 2012-03-13 2017-04-19 セイコーエプソン株式会社 Medical device using a fluid circulating device and the fluid circulation device
US9320846B2 (en) 2012-08-28 2016-04-26 Osprey Medical, Inc. Devices and methods for modulating medium delivery
US20160346462A1 (en) * 2014-02-11 2016-12-01 Smiths Medical Asd, Inc. Pump startup algorithms and related systems and methods
CN104225718A (en) * 2014-09-04 2014-12-24 西安力邦医疗电子有限公司 Bag type flexible balancing medical infusion pump

Citations (119)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US422936A (en) 1890-03-11 Frank
US1627257A (en) 1924-10-24 1927-05-03 Stevens Blamey Hydraulically-operated diaphragm pump
US2307566A (en) 1940-07-31 1943-01-05 Wright Aeronautical Corp Pneumatic drive fuel pump
US2315179A (en) 1939-12-18 1943-03-30 Universal Oil Prod Co Pumping of liquids
US2393838A (en) 1943-11-10 1946-01-29 Foundation For Clinical And Su Drop by drop pump
US2474512A (en) 1945-11-27 1949-06-28 Fluor Corp Pulsation elimination in fluid streams
US2565374A (en) 1949-11-30 1951-08-21 Standard Oil Dev Co Compounding of reciprocating pumps
US2773455A (en) 1953-06-25 1956-12-11 Mercier Jean Accumulator system for pressure surge relief
US2927658A (en) 1956-10-16 1960-03-08 Texaco Inc Reducing powder bulk
GB880192A (en) 1960-02-11 1961-10-18 Wilhelm Sydow Everett Fluid surge alleviator
US3252623A (en) 1965-07-22 1966-05-24 C F Liquidation Corp Apparatus for monitoring dispensing of liquid
US3527700A (en) 1968-06-06 1970-09-08 Baxter Laboratories Inc Dialysis fluid recirculation process and apparatus
DE1960369A1 (en) 1969-12-02 1971-06-09 Siemens Ag Device for damping the pulsation of a flowing liquid
US3658445A (en) 1969-06-12 1972-04-25 Prockter T Pulman Pumps
US3741692A (en) 1970-12-17 1973-06-26 Rupp Co Warren Surge suppressor for fluid lines
US3778195A (en) 1972-07-20 1973-12-11 G Bamberg Pump for parenteral injections and the like
US3804107A (en) 1972-04-05 1974-04-16 G Lisitsina Device for preparation of a dialyzing solution
US3818934A (en) 1973-03-09 1974-06-25 American Hospital Supply Corp Dampening unit for pulsatile pump
US3902490A (en) 1974-03-27 1975-09-02 Univ Utah Portable artificial kidney system
US3974854A (en) 1972-09-07 1976-08-17 Kurpanek W H Valve particularly adapted for utilization in controlling the flow of blood
US3986956A (en) 1973-12-04 1976-10-19 Tokyo Shibaura Electric Co., Ltd. Artificial kidney device
US4003379A (en) 1974-04-23 1977-01-18 Ellinwood Jr Everett H Apparatus and method for implanted self-powered medication dispensing
US4077405A (en) 1975-03-26 1978-03-07 Siemens Aktiengesellschaft Apparatus for infusing liquids into human or animal bodies
US4081372A (en) 1975-12-08 1978-03-28 University Of Utah Leakage indicator for recirculating peritoneal dialysis system
US4107039A (en) 1976-04-07 1978-08-15 Extracorporeal Medical Systems, Inc. Dialysate preparation system
US4191184A (en) 1977-01-06 1980-03-04 Carlisle Jeffrey A Intravenous infusion regulation system with reciprocal metering means
US4193068A (en) 1976-03-16 1980-03-11 Ziccardi John J Hemorrhage alarms
US4209014A (en) 1977-12-12 1980-06-24 Canadian Patents And Development Limited Dispensing device for medicaments
US4258711A (en) 1979-02-05 1981-03-31 Metal Bellows Corporation Infusion apparatus and method
US4264287A (en) 1978-07-28 1981-04-28 Nissan Motor Company, Limited Fuel pump assembly of fuel injection system
US4293961A (en) 1980-03-26 1981-10-13 Runge Thomas M Pulsatile flow cardiopulmonary bypass pump
US4345594A (en) 1980-09-12 1982-08-24 Institute Of Critical Care Medicine Closely controllable intravenous injection system
US4360324A (en) 1976-11-09 1982-11-23 Nikkiso, Co. Ltd. Pulsatile blood pump
US4360019A (en) 1979-02-28 1982-11-23 Andros Incorporated Implantable infusion device
US4392791A (en) * 1981-09-08 1983-07-12 Harold Mandroian Pressure pumping and priming pump apparatus
US4445829A (en) 1980-12-15 1984-05-01 Miller James D Apparatus for dampening pump pressure pulsations
WO1984001718A1 (en) 1982-11-04 1984-05-10 Univ Johns Hopkins Fluid handling system for medication infusion system
US4489750A (en) 1981-08-25 1984-12-25 Davol, Inc. Pressure operated pulsatile fluid flow device
US4493706A (en) 1982-08-12 1985-01-15 American Hospital Supply Corporation Linear peristaltic pumping apparatus and disposable casette therefor
US4501583A (en) 1983-06-15 1985-02-26 Extracorporeal, Inc. Hemodialysis access monitors
US4599165A (en) 1984-01-18 1986-07-08 Hospal Industrie Single-needle artificial kidney
US4604090A (en) 1983-11-22 1986-08-05 Consolidated Controls Corporation Compact implantable medication infusion device
US4610702A (en) 1983-05-10 1986-09-09 Industriell Arbetshygien I Soderhamn Ab Filter apparatus for air or gas purification
US4653987A (en) 1984-07-06 1987-03-31 Tsuyoshi Tsuji Finger peristaltic infusion pump
US4662829A (en) 1984-01-05 1987-05-05 C. R. Bard, Inc. Pulsatile pump
US4671792A (en) 1986-02-18 1987-06-09 American Hospital Supply Corporation Pressure-regulating peristaltic pump
US4673391A (en) 1983-05-31 1987-06-16 Koichi Sakurai Non-contact controlled micropump
US4684368A (en) 1984-06-01 1987-08-04 Parker Hannifin Corporation Inverted pump
US4687468A (en) 1984-10-01 1987-08-18 Cook, Incorporated Implantable insulin administration device
US4687423A (en) 1985-06-07 1987-08-18 Ivac Corporation Electrochemically-driven pulsatile drug dispenser
US4714462A (en) 1986-02-03 1987-12-22 Intermedics Infusaid, Inc. Positive pressure programmable infusion pump
US4728265A (en) 1987-01-30 1988-03-01 Fisher Scientific Group Inc. Peristaltic pump with cam action compensator
US4741678A (en) 1984-03-07 1988-05-03 C. R. Bard, Inc. Pulsatile pump
US4744786A (en) 1986-06-17 1988-05-17 Cordis Corporation Infusion pump
US4767526A (en) 1980-08-01 1988-08-30 Hospal Industrie Artificial kidney with automatic regulation of the pressure of the dialyslate as a function of withdrawal of ultrafiltrate
GB2181494B (en) 1985-10-03 1989-04-05 Draegerwerk Ag Piston dosing pump for a fluid
US4838887A (en) 1987-12-15 1989-06-13 Shiley Infusaid Inc. Programmable valve pump
US4871351A (en) 1984-09-28 1989-10-03 Vladimir Feingold Implantable medication infusion system
US4954046A (en) 1989-12-08 1990-09-04 Imed Corporation Peristaltic pump with mechanism for maintaining linear flow
US4969936A (en) 1989-12-26 1990-11-13 Westates Carbon Filtration apparatus
US4978338A (en) 1988-04-21 1990-12-18 Therex Corp. Implantable infusion apparatus
US4979441A (en) 1989-11-20 1990-12-25 Welch Elmer S Pulsation dampener
US5053031A (en) 1988-03-29 1991-10-01 Baxter International Inc. Pump infusion system
US5057081A (en) 1990-06-15 1991-10-15 Sherwood Medical Company Peristaltic infusion device
US5088904A (en) 1989-07-24 1992-02-18 Terumo Kabushiki Kaisha Transfusion pump
US5176644A (en) 1990-11-29 1993-01-05 Minimed Technologies, Ltd. Medication infusion pump with improved liquid-vapor pressure reservoir
US5183974A (en) 1992-04-03 1993-02-02 General Motors Corporation Gas pulsation attenuator for automotive air conditioning compressor
US5244463A (en) 1991-12-06 1993-09-14 Block Medical, Inc. Programmable infusion pump
US5247434A (en) 1991-04-19 1993-09-21 Althin Medical, Inc. Method and apparatus for kidney dialysis
US5263935A (en) 1986-11-26 1993-11-23 Baxter International Inc. Pressurized fluid dispenser
US5290158A (en) 1989-07-31 1994-03-01 Terumo Kabushiki Kaisha Peristaltic pump
US5387188A (en) 1993-05-10 1995-02-07 Pudenz-Schulte Medical Research Corporation Pulsatile flow-accommodating fluid shunt
US5421208A (en) 1994-05-19 1995-06-06 Baxter International Inc. Instantaneous volume measurement system and method for non-invasively measuring liquid parameters
US5522998A (en) 1993-03-18 1996-06-04 Fresenius Ag Hemodialysis apparatus having a single balance chamber and method of dialyzing blood therewith
US5544651A (en) 1992-09-08 1996-08-13 Wilk; Peter J. Medical system and associated method for automatic treatment
US5554011A (en) 1994-10-27 1996-09-10 Symbiosis Corporation Medical fluid pump powered by a constant source of vacuum
US5562429A (en) 1989-09-28 1996-10-08 Caro Manufacturing Corporation Pulse dampener and fuel pump having same
US5607418A (en) 1995-08-22 1997-03-04 Illinois Institute Of Technology Implantable drug delivery apparatus
GB2303925A (en) 1995-08-02 1997-03-05 Kodak Ltd Fluid delivery systems
US5730722A (en) 1992-08-19 1998-03-24 Wilk; Peter J. Method and apparatus for supplying a medical treatment composition to a patient
US5817076A (en) 1997-02-25 1998-10-06 Fard; Safieh Bahramian Toilet training diapers
US5868168A (en) 1997-08-04 1999-02-09 Hydril Company Pulsation dampener diaphragm
US5871478A (en) 1993-08-11 1999-02-16 Berrigan; Thomas John Implantable drug delivery means
US6058958A (en) 1998-11-05 2000-05-09 Micromed Technology, Inc. Pulsatile flow system and method
US6089837A (en) 1999-06-18 2000-07-18 Blacoh Fluid Control, Inc. Pump inlet stabilizer with a control unit for creating a positive pressure and a partial vacuum
US6159160A (en) 1998-03-26 2000-12-12 Ethicon, Inc. System and method for controlled infusion and pressure monitoring
US6234773B1 (en) 1994-12-06 2001-05-22 B-Braun Medical, Inc. Linear peristaltic pump with reshaping fingers interdigitated with pumping elements
US6280408B1 (en) 1992-11-09 2001-08-28 Anatole J. Sipin Controlled fluid transfer system
US6290681B1 (en) 1994-12-20 2001-09-18 Remote Medical Corporation Flow monitoring device for medical application
US6305919B1 (en) 1999-08-24 2001-10-23 Visteon Global Technologies, Inc. Hydraulic pump housing with an integral dampener chamber
US6312409B1 (en) 1996-12-31 2001-11-06 Elan Corporation, Plc Device for generating a pulsatile fluid drug flow
US6319245B1 (en) 1996-10-09 2001-11-20 Thomas John Berrigan Drug delivery means
US6386046B1 (en) 1999-09-28 2002-05-14 The Foxboro Company Method and system for characterizing pulsatile flow in a vortex flowmeter
US20020088752A1 (en) 2000-06-17 2002-07-11 Klaus Balschat Dialysis machine and method of operating a dialysis machine
US20020127736A1 (en) 2000-10-03 2002-09-12 California Institute Of Technology Microfluidic devices and methods of use
US6537268B1 (en) 1998-06-18 2003-03-25 Medtronic Minimed, Inc. Medical infusion device with a source of controlled compliance
US6558343B1 (en) 1998-04-02 2003-05-06 Debiotech S.A. Device for peritoneal dialysis and method for using said device
EP0816677B1 (en) 1996-07-03 2003-09-24 Seong-Cheol Kim Reciprocating pump
US20030195454A1 (en) 2002-04-10 2003-10-16 Ramesh Wariar Access disconnection systems and methods
US6638263B1 (en) 1999-10-12 2003-10-28 Durect Corporation Regulation of drug delivery through flow diversion
US6669455B2 (en) 2002-01-31 2003-12-30 Elmer Scott Welch Fluid-pumping system employing air-driven pump and employing at least one pulsation dampener
US20040019320A1 (en) 2002-07-19 2004-01-29 Childers Robert W. Systems and metods for performing peritoneal dialysis
US6723062B1 (en) 1999-09-03 2004-04-20 Baxter International Inc. Fluid pressure actuated blood pumping systems and methods with continuous inflow and pulsatile outflow conditions
US20040082903A1 (en) 2002-07-19 2004-04-29 Micheli Brian R. Systems and methods for peritoneal dialysis
US6746606B2 (en) 2002-01-11 2004-06-08 Delphi Technologies, Inc. Method and system for matching flow rate
US6837693B2 (en) 2002-01-31 2005-01-04 Ashear, Ltd. Fluid-pumping system employing piston-driven pump and employing at least one pulsation dampener
US20050038325A1 (en) 2003-08-13 2005-02-17 Bradley Jon Moll, Rodney L. Moll And Anne E. Moll Family Trust Method and device for monitoring loss of body fluid and dislodgment of medical instrument from body
US6861033B2 (en) 2001-01-05 2005-03-01 Gambro, Inc. Purified water supply system for high demand devices and applications
US6997942B2 (en) 1998-08-24 2006-02-14 Radiant Medical, Inc. Disposable cassette for intravascular heat exchange catheter
US7018361B2 (en) 2002-06-14 2006-03-28 Baxter International Inc. Infusion pump
US7025750B2 (en) 1999-11-03 2006-04-11 Dsu Medical Corporation Set for blood processing
US7048522B2 (en) 2003-05-28 2006-05-23 Bradford Jr Floyd John Fluid balanced pump
US7150711B2 (en) 2001-04-30 2006-12-19 Berlin Heart Ag Method for controlling an assist pump for fluid delivery systems with pulsatile pressure
US7175649B2 (en) 2000-02-28 2007-02-13 Radiant Medical, Inc. Method and system for control of a patient's body temperature by way of transluminally insertable heat exchange catheter
US20070135758A1 (en) 2000-02-10 2007-06-14 Baxter International Inc. Method and apparatus for monitoring and controlling peritoneal dialysis therapy
US7241378B2 (en) 2001-07-27 2007-07-10 Jms Co., Ltd. Hemodialysis apparatus
US20080015493A1 (en) 2003-11-05 2008-01-17 Baxter International Inc. Medical fluid pumping system having real time volume determination
US7326564B2 (en) 2001-02-20 2008-02-05 St. Jude Medical, Inc. Flow system for medical device evaluation and production
US7678070B2 (en) * 2004-11-30 2010-03-16 Atul Kumar System of dampening pressure pulsations caused by a positive displacement pump in endoscopic surgery

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6237773B1 (en) * 2000-06-02 2001-05-29 Goldman Toy Group, Inc. Toy with display card

Patent Citations (125)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US422936A (en) 1890-03-11 Frank
US1627257A (en) 1924-10-24 1927-05-03 Stevens Blamey Hydraulically-operated diaphragm pump
US2315179A (en) 1939-12-18 1943-03-30 Universal Oil Prod Co Pumping of liquids
US2307566A (en) 1940-07-31 1943-01-05 Wright Aeronautical Corp Pneumatic drive fuel pump
US2393838A (en) 1943-11-10 1946-01-29 Foundation For Clinical And Su Drop by drop pump
US2474512A (en) 1945-11-27 1949-06-28 Fluor Corp Pulsation elimination in fluid streams
US2565374A (en) 1949-11-30 1951-08-21 Standard Oil Dev Co Compounding of reciprocating pumps
US2773455A (en) 1953-06-25 1956-12-11 Mercier Jean Accumulator system for pressure surge relief
US2927658A (en) 1956-10-16 1960-03-08 Texaco Inc Reducing powder bulk
GB880192A (en) 1960-02-11 1961-10-18 Wilhelm Sydow Everett Fluid surge alleviator
US3252623A (en) 1965-07-22 1966-05-24 C F Liquidation Corp Apparatus for monitoring dispensing of liquid
US3527700A (en) 1968-06-06 1970-09-08 Baxter Laboratories Inc Dialysis fluid recirculation process and apparatus
US3658445A (en) 1969-06-12 1972-04-25 Prockter T Pulman Pumps
DE1960369A1 (en) 1969-12-02 1971-06-09 Siemens Ag Device for damping the pulsation of a flowing liquid
US3741692A (en) 1970-12-17 1973-06-26 Rupp Co Warren Surge suppressor for fluid lines
US3804107A (en) 1972-04-05 1974-04-16 G Lisitsina Device for preparation of a dialyzing solution
US3778195A (en) 1972-07-20 1973-12-11 G Bamberg Pump for parenteral injections and the like
US3974854A (en) 1972-09-07 1976-08-17 Kurpanek W H Valve particularly adapted for utilization in controlling the flow of blood
US3818934A (en) 1973-03-09 1974-06-25 American Hospital Supply Corp Dampening unit for pulsatile pump
US3986956A (en) 1973-12-04 1976-10-19 Tokyo Shibaura Electric Co., Ltd. Artificial kidney device
US3902490A (en) 1974-03-27 1975-09-02 Univ Utah Portable artificial kidney system
US4003379A (en) 1974-04-23 1977-01-18 Ellinwood Jr Everett H Apparatus and method for implanted self-powered medication dispensing
US4077405A (en) 1975-03-26 1978-03-07 Siemens Aktiengesellschaft Apparatus for infusing liquids into human or animal bodies
US4081372A (en) 1975-12-08 1978-03-28 University Of Utah Leakage indicator for recirculating peritoneal dialysis system
US4193068A (en) 1976-03-16 1980-03-11 Ziccardi John J Hemorrhage alarms
US4107039A (en) 1976-04-07 1978-08-15 Extracorporeal Medical Systems, Inc. Dialysate preparation system
US4360324A (en) 1976-11-09 1982-11-23 Nikkiso, Co. Ltd. Pulsatile blood pump
US4191184A (en) 1977-01-06 1980-03-04 Carlisle Jeffrey A Intravenous infusion regulation system with reciprocal metering means
US4209014A (en) 1977-12-12 1980-06-24 Canadian Patents And Development Limited Dispensing device for medicaments
US4264287A (en) 1978-07-28 1981-04-28 Nissan Motor Company, Limited Fuel pump assembly of fuel injection system
US4258711A (en) 1979-02-05 1981-03-31 Metal Bellows Corporation Infusion apparatus and method
US4360019A (en) 1979-02-28 1982-11-23 Andros Incorporated Implantable infusion device
US4525165A (en) 1979-04-27 1985-06-25 The Johns Hopkins University Fluid handling system for medication infusion system
US4293961A (en) 1980-03-26 1981-10-13 Runge Thomas M Pulsatile flow cardiopulmonary bypass pump
US4767526A (en) 1980-08-01 1988-08-30 Hospal Industrie Artificial kidney with automatic regulation of the pressure of the dialyslate as a function of withdrawal of ultrafiltrate
US4345594A (en) 1980-09-12 1982-08-24 Institute Of Critical Care Medicine Closely controllable intravenous injection system
US4445829A (en) 1980-12-15 1984-05-01 Miller James D Apparatus for dampening pump pressure pulsations
US4489750A (en) 1981-08-25 1984-12-25 Davol, Inc. Pressure operated pulsatile fluid flow device
US4392791A (en) * 1981-09-08 1983-07-12 Harold Mandroian Pressure pumping and priming pump apparatus
US4493706A (en) 1982-08-12 1985-01-15 American Hospital Supply Corporation Linear peristaltic pumping apparatus and disposable casette therefor
WO1984001718A1 (en) 1982-11-04 1984-05-10 Univ Johns Hopkins Fluid handling system for medication infusion system
US4610702A (en) 1983-05-10 1986-09-09 Industriell Arbetshygien I Soderhamn Ab Filter apparatus for air or gas purification
US4673391A (en) 1983-05-31 1987-06-16 Koichi Sakurai Non-contact controlled micropump
US4501583A (en) 1983-06-15 1985-02-26 Extracorporeal, Inc. Hemodialysis access monitors
US4604090A (en) 1983-11-22 1986-08-05 Consolidated Controls Corporation Compact implantable medication infusion device
US4662829A (en) 1984-01-05 1987-05-05 C. R. Bard, Inc. Pulsatile pump
US4599165A (en) 1984-01-18 1986-07-08 Hospal Industrie Single-needle artificial kidney
US4741678A (en) 1984-03-07 1988-05-03 C. R. Bard, Inc. Pulsatile pump
US4684368A (en) 1984-06-01 1987-08-04 Parker Hannifin Corporation Inverted pump
US4653987A (en) 1984-07-06 1987-03-31 Tsuyoshi Tsuji Finger peristaltic infusion pump
US4871351A (en) 1984-09-28 1989-10-03 Vladimir Feingold Implantable medication infusion system
US4687468A (en) 1984-10-01 1987-08-18 Cook, Incorporated Implantable insulin administration device
US4687423A (en) 1985-06-07 1987-08-18 Ivac Corporation Electrochemically-driven pulsatile drug dispenser
GB2181494B (en) 1985-10-03 1989-04-05 Draegerwerk Ag Piston dosing pump for a fluid
US4714462A (en) 1986-02-03 1987-12-22 Intermedics Infusaid, Inc. Positive pressure programmable infusion pump
US4671792A (en) 1986-02-18 1987-06-09 American Hospital Supply Corporation Pressure-regulating peristaltic pump
US4744786A (en) 1986-06-17 1988-05-17 Cordis Corporation Infusion pump
US5263935A (en) 1986-11-26 1993-11-23 Baxter International Inc. Pressurized fluid dispenser
US4728265A (en) 1987-01-30 1988-03-01 Fisher Scientific Group Inc. Peristaltic pump with cam action compensator
US4838887A (en) 1987-12-15 1989-06-13 Shiley Infusaid Inc. Programmable valve pump
US5053031A (en) 1988-03-29 1991-10-01 Baxter International Inc. Pump infusion system
US4978338A (en) 1988-04-21 1990-12-18 Therex Corp. Implantable infusion apparatus
US5152680A (en) 1989-07-24 1992-10-06 Terumo Kabushiki Kaisha Transfusion pump
US5088904A (en) 1989-07-24 1992-02-18 Terumo Kabushiki Kaisha Transfusion pump
US5290158A (en) 1989-07-31 1994-03-01 Terumo Kabushiki Kaisha Peristaltic pump
US5562429A (en) 1989-09-28 1996-10-08 Caro Manufacturing Corporation Pulse dampener and fuel pump having same
US4979441A (en) 1989-11-20 1990-12-25 Welch Elmer S Pulsation dampener
US4954046A (en) 1989-12-08 1990-09-04 Imed Corporation Peristaltic pump with mechanism for maintaining linear flow
US4969936A (en) 1989-12-26 1990-11-13 Westates Carbon Filtration apparatus
US5057081A (en) 1990-06-15 1991-10-15 Sherwood Medical Company Peristaltic infusion device
US5176644A (en) 1990-11-29 1993-01-05 Minimed Technologies, Ltd. Medication infusion pump with improved liquid-vapor pressure reservoir
US5247434A (en) 1991-04-19 1993-09-21 Althin Medical, Inc. Method and apparatus for kidney dialysis
US5244463A (en) 1991-12-06 1993-09-14 Block Medical, Inc. Programmable infusion pump
US5183974A (en) 1992-04-03 1993-02-02 General Motors Corporation Gas pulsation attenuator for automotive air conditioning compressor
US5730722A (en) 1992-08-19 1998-03-24 Wilk; Peter J. Method and apparatus for supplying a medical treatment composition to a patient
US5544651A (en) 1992-09-08 1996-08-13 Wilk; Peter J. Medical system and associated method for automatic treatment
US6280408B1 (en) 1992-11-09 2001-08-28 Anatole J. Sipin Controlled fluid transfer system
US5522998A (en) 1993-03-18 1996-06-04 Fresenius Ag Hemodialysis apparatus having a single balance chamber and method of dialyzing blood therewith
US5387188A (en) 1993-05-10 1995-02-07 Pudenz-Schulte Medical Research Corporation Pulsatile flow-accommodating fluid shunt
US7018375B2 (en) 1993-08-11 2006-03-28 Thomas John Berrigan Drug delivery device
US5871478A (en) 1993-08-11 1999-02-16 Berrigan; Thomas John Implantable drug delivery means
US6471686B1 (en) 1993-08-11 2002-10-29 Thomas John Berrigan Drug delivery device
US5421208A (en) 1994-05-19 1995-06-06 Baxter International Inc. Instantaneous volume measurement system and method for non-invasively measuring liquid parameters
US5554011A (en) 1994-10-27 1996-09-10 Symbiosis Corporation Medical fluid pump powered by a constant source of vacuum
US6234773B1 (en) 1994-12-06 2001-05-22 B-Braun Medical, Inc. Linear peristaltic pump with reshaping fingers interdigitated with pumping elements
US6290681B1 (en) 1994-12-20 2001-09-18 Remote Medical Corporation Flow monitoring device for medical application
GB2303925A (en) 1995-08-02 1997-03-05 Kodak Ltd Fluid delivery systems
US5607418A (en) 1995-08-22 1997-03-04 Illinois Institute Of Technology Implantable drug delivery apparatus
EP0816677B1 (en) 1996-07-03 2003-09-24 Seong-Cheol Kim Reciprocating pump
US6319245B1 (en) 1996-10-09 2001-11-20 Thomas John Berrigan Drug delivery means
US6312409B1 (en) 1996-12-31 2001-11-06 Elan Corporation, Plc Device for generating a pulsatile fluid drug flow
US5817076A (en) 1997-02-25 1998-10-06 Fard; Safieh Bahramian Toilet training diapers
US5868168A (en) 1997-08-04 1999-02-09 Hydril Company Pulsation dampener diaphragm
US6159160A (en) 1998-03-26 2000-12-12 Ethicon, Inc. System and method for controlled infusion and pressure monitoring
US6558343B1 (en) 1998-04-02 2003-05-06 Debiotech S.A. Device for peritoneal dialysis and method for using said device
US6537268B1 (en) 1998-06-18 2003-03-25 Medtronic Minimed, Inc. Medical infusion device with a source of controlled compliance
US6997942B2 (en) 1998-08-24 2006-02-14 Radiant Medical, Inc. Disposable cassette for intravascular heat exchange catheter
US6058958A (en) 1998-11-05 2000-05-09 Micromed Technology, Inc. Pulsatile flow system and method
US6089837A (en) 1999-06-18 2000-07-18 Blacoh Fluid Control, Inc. Pump inlet stabilizer with a control unit for creating a positive pressure and a partial vacuum
US6305919B1 (en) 1999-08-24 2001-10-23 Visteon Global Technologies, Inc. Hydraulic pump housing with an integral dampener chamber
US6723062B1 (en) 1999-09-03 2004-04-20 Baxter International Inc. Fluid pressure actuated blood pumping systems and methods with continuous inflow and pulsatile outflow conditions
US6386046B1 (en) 1999-09-28 2002-05-14 The Foxboro Company Method and system for characterizing pulsatile flow in a vortex flowmeter
US6638263B1 (en) 1999-10-12 2003-10-28 Durect Corporation Regulation of drug delivery through flow diversion
US7025750B2 (en) 1999-11-03 2006-04-11 Dsu Medical Corporation Set for blood processing
US20070135758A1 (en) 2000-02-10 2007-06-14 Baxter International Inc. Method and apparatus for monitoring and controlling peritoneal dialysis therapy
US7175649B2 (en) 2000-02-28 2007-02-13 Radiant Medical, Inc. Method and system for control of a patient's body temperature by way of transluminally insertable heat exchange catheter
US20020088752A1 (en) 2000-06-17 2002-07-11 Klaus Balschat Dialysis machine and method of operating a dialysis machine
US20020127736A1 (en) 2000-10-03 2002-09-12 California Institute Of Technology Microfluidic devices and methods of use
US6861033B2 (en) 2001-01-05 2005-03-01 Gambro, Inc. Purified water supply system for high demand devices and applications
US7326564B2 (en) 2001-02-20 2008-02-05 St. Jude Medical, Inc. Flow system for medical device evaluation and production
US7150711B2 (en) 2001-04-30 2006-12-19 Berlin Heart Ag Method for controlling an assist pump for fluid delivery systems with pulsatile pressure
US7241378B2 (en) 2001-07-27 2007-07-10 Jms Co., Ltd. Hemodialysis apparatus
US6746606B2 (en) 2002-01-11 2004-06-08 Delphi Technologies, Inc. Method and system for matching flow rate
US6837693B2 (en) 2002-01-31 2005-01-04 Ashear, Ltd. Fluid-pumping system employing piston-driven pump and employing at least one pulsation dampener
US6669455B2 (en) 2002-01-31 2003-12-30 Elmer Scott Welch Fluid-pumping system employing air-driven pump and employing at least one pulsation dampener
US20030195454A1 (en) 2002-04-10 2003-10-16 Ramesh Wariar Access disconnection systems and methods
US7018361B2 (en) 2002-06-14 2006-03-28 Baxter International Inc. Infusion pump
US20070158267A1 (en) 2002-07-19 2007-07-12 Baxter International Inc. Systems and methods for peritoneal dialysis
US20040019320A1 (en) 2002-07-19 2004-01-29 Childers Robert W. Systems and metods for performing peritoneal dialysis
US7208092B2 (en) 2002-07-19 2007-04-24 Baxter International Inc. Systems and methods for peritoneal dialysis
US20040082903A1 (en) 2002-07-19 2004-04-29 Micheli Brian R. Systems and methods for peritoneal dialysis
US7048522B2 (en) 2003-05-28 2006-05-23 Bradford Jr Floyd John Fluid balanced pump
US20050038325A1 (en) 2003-08-13 2005-02-17 Bradley Jon Moll, Rodney L. Moll And Anne E. Moll Family Trust Method and device for monitoring loss of body fluid and dislodgment of medical instrument from body
US20080015493A1 (en) 2003-11-05 2008-01-17 Baxter International Inc. Medical fluid pumping system having real time volume determination
US7678070B2 (en) * 2004-11-30 2010-03-16 Atul Kumar System of dampening pressure pulsations caused by a positive displacement pump in endoscopic surgery

Non-Patent Citations (5)

* Cited by examiner, † Cited by third party
Title
International Search Report and Written Opinion for International Application No. PCT/US2009/030299 mailed on May 29, 2009.
International Search Report and Written Opinion for International Application No. PCT/US2009/047585 dated Feb. 1, 2010.
International Search Report and Written Opinion for International Application No. PCT/US2011/023158 dated May 9, 2011.
International Search Report and Written Opinion for PCT/US2008/066101 mailed Feb. 12, 2009.
Non-Final Office Action for U.S. Appl. No. 12/180,324 dated Aug. 12, 2010.

Also Published As

Publication number Publication date Type
WO2009065153A8 (en) 2009-10-08 application
US20090131859A1 (en) 2009-05-21 application
WO2009065153A3 (en) 2009-07-16 application
WO2009065153A2 (en) 2009-05-22 application
EP2496284A2 (en) 2012-09-12 application

Similar Documents

Publication Publication Date Title
US3298367A (en) Apparatus for administering parenteral liquids
US5190522A (en) Device for monitoring the operation of a delivery system and the method of use thereof
US7008403B1 (en) Infusion pump and method for use
US4714462A (en) Positive pressure programmable infusion pump
US6280408B1 (en) Controlled fluid transfer system
US6198966B1 (en) Recirculating implantable drug delivery system
US20050214129A1 (en) Medical infusion pump with closed loop stroke feedback system and method
US6398760B1 (en) Volumetric infusion pump with servo valve control
US4921480A (en) Fixed volume infusion device
US20060181695A1 (en) Compensating liquid delivery system and method
US5356376A (en) Flow controllers for fluid infusion sets
US20020156464A1 (en) Non-constant pressure infusion pump
US7311693B2 (en) Drug delivery device and method
US6030359A (en) Apparatus and method for delivering fluid flow to a surgical site
US4784576A (en) Pump pressure sensor
US7004924B1 (en) Methods, systems, and kits for the extracorporeal processing of blood
US5267964A (en) Fluid control device including automatic valve
US5720721A (en) Method for monitoring viscosity and occlusions in an enteral feeding pump delivery
US20060122556A1 (en) Low turbulence fluid management system for endoscopic procedures
US4770168A (en) Electrically controllable anesthesia vaporizer
US6485464B1 (en) Reduced height implantable drug infusion device
US4180067A (en) Apparatus for delivering fluids with controlled rates of flow
US20070062251A1 (en) Infusion Pump With Closed Loop Control and Algorithm
US7367968B2 (en) Implantable pump with adjustable flow rate
US5378227A (en) Biological/pharmaceutical method and apparatus for collecting and mixing fluids

Legal Events

Date Code Title Description
AS Assignment

Owner name: BAXTER INTERNATIONAL INC., ILLINOIS

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:DELCASTILLO, JORGE;AKONUR, ALP;REEL/FRAME:020185/0460

Effective date: 20071114

Owner name: BAXTER HEALTHCARE S. A., SWITZERLAND

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:DELCASTILLO, JORGE;AKONUR, ALP;REEL/FRAME:020185/0460

Effective date: 20071114

AS Assignment

Owner name: BAXTER HEALTHCARE S.A., SWITZERLAND

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:DELCASTILLO, JORGE;AKONUR, ALP;REEL/FRAME:020194/0619

Effective date: 20071114

Owner name: BAXTER INTERNATIONAL INC., ILLINOIS

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:DELCASTILLO, JORGE;AKONUR, ALP;REEL/FRAME:020194/0619

Effective date: 20071114

AS Assignment

Owner name: BAXTER HEALTHCARE S.A., SWITZERLAND

Free format text: CERTIFICATE OF CHANGE OF CORPORATE ADDRESS;ASSIGNOR:BAXTER HEALTHCARE S.A.;REEL/FRAME:030312/0343

Effective date: 20090828

FPAY Fee payment

Year of fee payment: 4